Hearing aid method for in-situ occlusion effect and directly transmitted sound measurement

• US 8,059,847 B2
• Filed: 01/29/2009
• Issued: 11/15/2011
• Est. Priority Date: 08/07/2006
• Status: Active Grant

• Current Assignee: Widex A/S (WS Audiology A/S)
• Original Assignee: Widex A/S (WS Audiology A/S)
• Inventors: Nordahn, Morten Agerbak
• Primary Examiner(s): Ni; Suhan
• Application Number:
  US12/362,112
• Publication Number:
  US 20090129619A1
• Time in Patent Office: 1,020 Days
• Field of Search: 381/23.1, 381/60, 381/312, 381316-318, 381/322, 381/328
• US Class Current: 381/328
• CPC Class Codes: H04R 2460/11 Aspects relating to vents, e.g. shape, orientation, acoustic properties in ear tips of hearing devices to prevent occlusion
• CPC Class Codes: H04R 25/70 Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting

Abstract

A hearing aid (100) comprises at least one first microphone (10) generating a first input signal from sounds external to a user of the hearing aid, signal processing means, a receiver (30) and, a second microphone (40) generating a second input signal from sounds in the occluded ear of the user. In a measurement mode the signal processing means produces an occlusion effect value or directly transmitted sound value from the difference between the sound levels of the second and the first input signals generated both at the same time while the receiver is silent. The invention further provides a system and a method for determining an occlusion effect and a directly transmitted sound value.

Claims

1. A hearing aid for measurement of in-situ occlusion effect or directly transmitted sound, said hearing aid comprising:

a first microphone adapted to generate a first input signal from sounds external to a user of the hearing aid;

a signal processing means;

a receiver; and

a second microphone adapted to generate a second input signal from sounds in the occluded ear of the user;

said signal processing means being adapted to generate a hearing loss compensated electric output signal from said first input signal, and said receiver being adapted to produce an acoustic output signal from said electric output signal; and

said hearing aid being adapted to selectively enter a measurement mode, in which said mode receiver is silent and said signal processing means is adapted to produce at least one occlusion effect value or at least one directly transmitted sound value from the difference between simultaneously generated sound levels of the second and the first input signals.

2. The hearing aid according to claim 1, further comprising interface means for connection to a fitting device and adapted to transmit said input signals, said occlusion effect values, and said directly transmitted sound values for further processing in said fitting device.

3. The hearing aid of claim 1 comprising a band split filter, said band split filter being adapted to convert said first and second input signals into first and second band-split input signals, respectively, in a plurality of frequency bands comprising at least one frequency band below approximately 1 kHz.

4. The hearing aid according to claim 1, wherein in said measurement mode said receiver is used as said second microphone generating said second input signal.

5. The hearing aid according to claim 1, wherein said hearing aid is a behind-the-ear hearing aid and said second microphone is a built-in microphone of the hearing aid, associated with a probe tube having a first end being coupled to said second microphone and a second end being inserted into the ear canal of the user, and being adapted to propagate sounds in the occluded ear to the second microphone.

6. The hearing aid according to claim 1, wherein said hearing aid is an in-the-ear or completely-in-the-canal hearing aid and said second microphone is a built-in microphone at a receiver side of the hearing aid.

7. A hearing aid system for measurement of occlusion effect or directly transmitted sound, the system comprising a pair of a first hearing aid for one ear of a user and a second hearing aid for the other ear of the user, wherein said first hearing aid comprises:

a first microphone adapted to generate a first input signal from sounds external to a user of the first hearing aid;

a first signal processing means; and

a first receiver;

wherein said second hearing aid comprises;

a second microphone;

a second signal processing means; and

a second receiver;

said first signal processing means being adapted to generate a hearing loss compensated electric output signal from said first input signal, and said first receiver is adapted to produce a first acoustic output signal from said electric output signal; and

wherein said system is adapted to selectively enter a measurement mode wherein said second microphone is adapted to generate a second input signal from sounds in the occluded ear of the user, said second receiver is silent and one of said first or second signal processing means is adapted to produce at least one occlusion effect value or at least one directly transmitted sound from the difference between simultaneously generated sound levels of the second and the first input signals.

8. The system of claim 7, wherein said second hearing aid comprises a second band split filter, said second band split filters being adapted to convert said second input signal into second band-split input signals in a plurality of respective frequency bands comprising at least one frequency band below approximately 1 kHz.

9. The system according to claim 7, wherein said second microphone is associated with a probe tube inserted into the ear canal of the user, said probe tube being adapted to propagate sounds in the occluded ear to said second microphone.

10. The system according to claim 8, comprising detection means adapted to determine whether in at least one frequency band the sound level of the second input signal is larger than that of the first input signal in the measurement mode and if this is the case to classify the input signals as valid for occlusion effect calculation.

11. The system according to claim 10, wherein if in at least one frequency band the sound level of the second input signal is smaller than that of the first input signal, the detection means is adapted to classify the input signals as valid for calculating a value of the directly transmitted sound from the second and the first input signals.

12. A method for measurement of in-situ occlusion effect or direct transmission sound by means of a hearing aid having a first microphone for generating a first input signal from sounds external to a user of the hearing aid and a receiver, said method comprising the steps of:

generating a hearing loss compensated output signal from said first input signal output by the receiver in a normal hearing aid mode;

switching said hearing aid from said normal hearing aid mode into a measurement mode, causing said receiver to be silent, and carrying out the following steps;

simultaneously generating said first input signal and a second input signal, wherein said second input signal is generated by a second microphone from sounds in the occluded ear of the user; and

calculating at least one occlusion effect or directly transmitted sound value from the difference between the sound levels of said second and first input signals.

13. The method according to claim 12 comprising converting said first and second input signals into first and second band split input signals, in a plurality of respective frequency bands comprising at least one frequency band below approximately 1 kHz;

and calculating at least one occlusion effect or directly transmitted sound value from the difference between the sound levels of said second and first input signal of a frequency band below 1 kHz.

14. The method according to claim 12, wherein said receiver is used as said second microphone generating said second input signal in said measurement mode.

15. The method according to claim 12, wherein said method uses a pair of a first hearing aid for one ear of a user and of a second hearing aid for the other ear of the user for occlusion effect measurement, wherein said first input signal is generated by said first hearing aid and said second input signal is generated by said second hearing aid.

16. A method for fitting a hearing aid to a user, said hearing aid having a first microphone for generating a first input signal from sounds external to a user of the hearing aid and a receiver, said method comprising the steps of:

generating a hearing loss compensated output signal from said first input signal output by the receiver in a normal hearing aid mode;

switching said hearing aid from said normal hearing aid mode into a measurement mode, causing said receiver to be silent, and carrying out the following steps;

simultaneously generating said first input signal and a second input signal, wherein said second input signal is generated by a second microphone from sounds in the occluded ear of the user;

calculating at least one occlusion effect or directly transmitted sound value from the difference between the sound levels of said second and first band-split input signals; and

fitting said hearing aid based on at least one of said occlusion effect value and said directly transmitted sound value.

17. A method for vent size determination for a hearing aid by means of in-situ occlusion effect measurement,

said hearing aid having a first microphone for generating a first input signal from sounds external to a user of the hearing aid and a receiver, said method comprising the steps of:

providing an ear of a user with a prospective hearing aid, said prospective hearing aid occluding said ear of the user;

generating a hearing loss compensated output signal from said first input signal output by the receiver in a normal hearing aid mode;

switching said hearing aid from said normal hearing aid mode into a measurement mode, causing said receiver to be silent, and carrying out the following steps;

simultaneously generating said first input signal and a second input signal, wherein said second input signal is generated by a second microphone from sounds in the occluded ear of the user;

calculating at least one occlusion effect or directly transmitted sound value from the difference between the sound levels of said second and first input signals; and

determining the vent size for said hearing aid based on at least one of the calculated occlusion effect and the directly transmitted sound value.

18. The method according to claim 17, wherein the ear of the user is occluded by a soft plug inserted into the ear canal of the user.

19. The method according to claim 17, wherein the step of determining the vent size comprises:

measuring at least one transfer function of said hearing aid;

estimating an effective vent size for said hearing aid by determining that vent size as said effective vent size that provides the best fit between a number of predetermined transfer function values and the measured transfer function;

calculating the vent effect corresponding to the said effective vent size and a number of other vent sizes;

determining the preferred reduction in occlusion effect in at least one band, such that said occlusion effect is below 8 dB in at least one band;

using the information provided by said calculated vent effect to determine a second effective vent size, which has a vent effect which corresponds to the preferred reduction in occlusion effect; and

using said second vent size as a recommendation for vent modification to obtain an occlusion effect which is convenient for the user.

20. A system for measurement of in-situ occlusion effect or directly transmitted sound by use of a hearing aid, the hearing aid having a first microphone adapted to generate a first input signal from sounds external to a user of the hearing aid;

a signal processing means;

a receiver; and

a second microphone adapted to generate a second input signal from sounds in the occluded ear of the user;

said signal processing means being adapted in a normal hearing aid mode to generate a hearing loss compensated electric output signal from said first input signal, and said receiver being adapted to produce an acoustic output signal from said electric output signal;

said system comprising a data processing system; and

a computer program, which when executed on said data processing system enables the system to switch said hearing aid from said normal hearing aid mode into a measurement mode, causing said receiver to be silent, and carrying out the following steps;

simultaneously generating said first input signal and a second input signal, wherein said second input signal is generated by a second microphone from sounds in the occluded ear of the user;

and calculating at least one occlusion effect or directly transmitted sound value from the difference between the sound levels of said second and first band-split input signals.